WO2021081671A1 - Système et procédé pour effectuer une dosimétrie de bruit intra-auriculaire et une évaluation d'affaiblissement personnelle sous un bouchon d'oreille électro-acoustique tout en excluant les perturbations induites par le porteur et en séparant les sources d'exposition - Google Patents

Système et procédé pour effectuer une dosimétrie de bruit intra-auriculaire et une évaluation d'affaiblissement personnelle sous un bouchon d'oreille électro-acoustique tout en excluant les perturbations induites par le porteur et en séparant les sources d'exposition Download PDF

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Publication number
WO2021081671A1
WO2021081671A1 PCT/CA2020/051481 CA2020051481W WO2021081671A1 WO 2021081671 A1 WO2021081671 A1 WO 2021081671A1 CA 2020051481 W CA2020051481 W CA 2020051481W WO 2021081671 A1 WO2021081671 A1 WO 2021081671A1
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WO
WIPO (PCT)
Prior art keywords
spl
sound
iels
playback
ear canal
Prior art date
Application number
PCT/CA2020/051481
Other languages
English (en)
Inventor
Jérémie VOIX
Antoine Bernier
Fabien Bonnet
Original Assignee
École De Technologie Supérieure
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by École De Technologie Supérieure filed Critical École De Technologie Supérieure
Priority to EP20881596.9A priority Critical patent/EP4052028A4/fr
Priority to US17/758,988 priority patent/US20230035275A1/en
Publication of WO2021081671A1 publication Critical patent/WO2021081671A1/fr

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R29/00—Monitoring arrangements; Testing arrangements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F11/00—Methods or devices for treatment of the ears or hearing sense; Non-electric hearing aids; Methods or devices for enabling ear patients to achieve auditory perception through physiological senses other than hearing sense; Protective devices for the ears, carried on the body or in the hand
    • A61F11/06—Protective devices for the ears
    • A61F11/08—Protective devices for the ears internal, e.g. earplugs
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/16—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/175—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound
    • G10K11/178—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase
    • G10K11/1785—Methods, e.g. algorithms; Devices
    • G10K11/17853—Methods, e.g. algorithms; Devices of the filter
    • G10K11/17854—Methods, e.g. algorithms; Devices of the filter the filter being an adaptive filter
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/10—Earpieces; Attachments therefor ; Earphones; Monophonic headphones
    • H04R1/1083—Reduction of ambient noise

Definitions

  • the present invention generally relates to methods and systems to measure the sound exposure under an electro-acoustic earplug as well as the personal attenuation rating (PAR) provided by the earplug. More specifically, the present invention relates to methods and systems for estimating the in-ear noise exposure from the earplug’s receiver and/or the environment while excluding the noise contributions from the wearer (termed “wearer-induced disturbances). The present invention further relates to methods enabling estimation of the PAR, such as in the context of implementation on embedded computing platforms.
  • NIHL noise induced hearing loss
  • HPDs hearing protection devices
  • a given HPD can be a poorly suited choice, depending on the initial noise level that it attempts to reduce, if it under attenuates and lets dangerous noise exposure dose still occur.
  • a given HPD can be inadequate if it over-attenuates, leading to poor situational awareness and communication difficulties that may cause workers to occasionally remove of their HPDs while still subjected to high noise levels, leading to dangerous noise exposure dose.
  • Even if an HPD is theoretically suitable, it can often be improperly fitted and under-perform. Additionally, the background noise level may rise above expectations and make a previously suitable HPD no longer adequate.
  • IEM inner ear microphone
  • in-ear SPL While they contribute to in-ear SPL, it is possible that such disturbances may need to be treated differently than other sources due notably to the acoustic stapedius reflex, which reduces hearing sensitivity by up to 15 dB and has been shown to trigger when one speaks.
  • current in-ear dosimeters are not designed to be compatible with advanced hearing protection featuring an in-ear loudspeaker (IELS), which can be used for playback of communication and audio signals and, in combination with an outer ear microphone (OEM), can also be used to offer level dependent attenuation.
  • IELS in-ear loudspeaker
  • OEM outer ear microphone
  • in-ear dosimeters do not allow segregation of the contribution of the various sound sources that contribute to the in-ear SPL, which can offer insight to come up with a suitable palliative strategy when the sound exposure limit is exceeded. [0006] There is thus a need for a method or a system to measure the in-ear noise exposure under an advanced HPD while segregating the contributions of wearer-induced disturbances, communication and audio signals and level dependent attenuation.
  • a method to perform in-ear noise dosimetry and personal attenuation rating under an electro-acoustic earplug while excluding wearer- induced disturbances and separating exposure sources using models of electro-acoustical paths to separate the contributions of sound exposure from various sources and provide dosimetry is provided.
  • the method may further comprise applying different corrections, depending on the type of source, to each of separated contributions to obtain better accuracy by correcting the signals obtained at the IEM so that they better represent the signal that is inside the ear canal, at the inner-end of the ear tip.
  • the method may comprise using a FIR modeling the transfer function of the earpiece and a source signal provided by an OEM to estimate an IEM signal as a method for WID and playback segregation in the context of dosimetry.
  • the method may comprise using a FIR modeling of the transfer function between the loudspeaker and the IEM to filter incoming audio signal destined for playback as a method for WID and residual ambient segregation in the context of dosimetry.
  • the method may further comprise subtracting the estimates of an IEM signal as a method for WID and playback segregation in the context of dosimetry and residual ambient segregation in the context of dosimetry from the IEM to isolate the contribution of WID.
  • the method comprises strategies to manage WID contribution to sound exposure in the context of dosimetry, such as including it to the total dose, excluding it, weighting it, or any combination thereof.
  • the method further comprises temporarily weighting the contribution of all sources when significant WID energy is present to consider the effect of inhibition mechanisms such as the stapedius reflex, triggered by high level WID.
  • the method may also use the OEM and the IEM estimates to calculate a PAR in real-time that accounts for spectral uncertainty.
  • a system to measure noise reduction and evaluate contributions of various sound sources to a sound dose comprise a hearing protection device (HPD) comprising a passive attenuation device adapted to reduce ambient sound present outside an ear of a wearer of the HPD, an inner ear microphone (IEM) adapted to capture a general sound pressure level (SPL) of the sound dose present in the ear canal, outer ear microphone (OEM) adapted to capture the ambient sound, an in-ear loudspeaker (IELS) configured to emit a playback signal in an ear canal of a wearer according to at least one sound source.
  • HPD hearing protection device
  • IEM inner ear microphone
  • OEM outer ear microphone
  • IELS in-ear loudspeaker
  • the system further comprising a processor in signal communication with the IEM and the OEM, the processor being configured to estimate at least one specific SPL corresponding to an identified sound component of the sound dose in the ear canal.
  • the processor may further be in signal communication with the IELS and the at least one specific SPL is a playback SPL, the processor being configured to compute an estimate value of the playback SPL according to the at least one sound source.
  • the estimate value of the playback SPL may be computed according to at least one IELS-IEM model.
  • the at least one IELS-IEM model may be an adaptive digital filter.
  • the playback signal may be emitted according to a plurality of sound sources.
  • the at least one specific SPL may be a residual ambient SPL, the processor being configured to compute an estimate value of the residual ambient SPL according to the ambient sound captured by the OEM.
  • the estimate value of the residual ambient SPL may be computed according to at least one passive attenuation model.
  • the at least one passive attenuation model may be an adaptive digital filter.
  • the processor may be further configured to subtract each of the at least one estimated specific SPL from the general SPL. The remainder of the subtraction may be an estimation of a wearer-induced disturbances (WID) SPL present in the ear canal.
  • WID wearer-induced disturbances
  • the processor may be further configured to compute a correction for each of the at least one estimated specific SPL.
  • the processor may be further configured to process each of the plurality of sound sources according to a corresponding one of the at least one IELS-IEM model.
  • the plurality of sound sources may be at least one of an audio signal, a communication signal or a level-controlled output of the OEM.
  • the HPD may further comprise an audio mixer adapted to combine the plurality of sound sources.
  • the HPD may further comprise a digital sound processor configured to receive the playback signal as input.
  • the processor may be further configured to compute an OEM A-weighting according to the ambient sound captured by the OEM and to compute an estimated residual ambient A-weighting according to the estimated residual ambient SPL.
  • the processor may be further configured to compute a personal attenuation rating (PAR) estimate by subtracting the estimated residual ambient A-weighting from the OEM A-weighting.
  • PAR personal attenuation rating
  • the system may further comprise a diagnostic module configured to receive the at least one estimated specific SPL.
  • the diagnostic module may be configured to recommend at least one action to be executed by the wearer to reduce the sound dose in the ear canal.
  • a method to measure noise reduction and evaluate contributions of various sound sources of a sound dose in an ear canal of a wearer comprises capturing the sound dose in the ear canal, the sound dose comprising at least one sound component, estimating a specific canal SPL of the at least one sound component and subtracting the estimated specific canal SPL from the captured sound dose for each of the at least one sound component.
  • the method may further comprise capturing an ambient sound pressure level (SPL) outside the ear of the wearer and wherein the estimated specific canal SPL is an estimate of the residual ambient SPL present in the ear canal and the estimating is further performed according to the captured sound dose.
  • the estimating may be further performed according to at least one passive attenuation model.
  • the method may further comprise removing the estimated residual ambient SPL from the captured sound dose or may comprise determining an estimation of wearer-induced disturbances (WID) SPL present in the ear canal according to a remainder of the removing.
  • WID wearer-induced disturbances
  • the method may further comprising emitting an IELS playback signal in the ear canal according to at least one sound source and wherein the estimated specific canal SPL is a playback SPL present in the ear canal and produced by the emitting.
  • the estimating may be further performed by one or more IELS-IEM model.
  • the IELS playback signal may be emitted according to a plurality of sound sources, the estimating comprising estimating one specific canal playback SPL for each of the plurality of sound sources.
  • the estimating may be further performed by one or more IELS-IEM model for each of the plurality of sound sources signal.
  • the method may comprise mixing the plurality of sound sources to generate the IELS playback signal or may comprise removing the estimated IELS playback SPL from the captured sound dose.
  • the method may further comprise estimating of wearer-induced disturbances (WID) SPL present in the ear canal according to the removing.
  • the method may further comprise digitally processing the emitted IELS playback signal.
  • WID wearer-induced disturbances
  • the method may further comprise emitting an IELS playback signal in the ear canal according to at least one sound source, estimating the playback SPL present in the ear canal according to from the at least one sound sources, removing the estimated residual ambient SPL and the estimated playback SPL from the captured sound dose and estimating wearer-induced disturbances (WID) SPL present in the ear canal according to the removing.
  • the method may further comprise calculating an OEM A-weighting according to the captured ambient SPL and calculating a canal A-weighting according to the estimated residual ambient SPL.
  • the method may further comprise calculating a personal attenuation rating (PAR) estimate by subtracting the canal A-weighting from the OEM A- weighting.
  • the method may further comprise recommending at least one action to be executed by the wearer to reduce the sound dose in the ear canal according to the estimated specific canal SPL.
  • PAR personal attenuation rating
  • a system to measure noise reduction and evaluate contributions of residual ambient sound pressure level (SPL) of a sound dose present in an ear canal comprises a hearing protection device (HPD) comprising a passive attenuation device adapted to reduce ambient sound present outside an ear of a wearer of the HPD, an inner ear microphone (IEM) adapted to capture canal sound pressure level (SPL) of the sound dose present in the ear canal, an outer ear microphone (OEM) adapted to capture the ambient sound.
  • HPD hearing protection device
  • IEM inner ear microphone
  • OEM outer ear microphone
  • the system further comprises a processor in signal communication with the IEM and the OEM, the processor being configured to compute an estimate of the residual ambient SPL of the sound dose in the ear canal.
  • the estimate of the residual ambient SPL may be computed according to one or more passive attenuation models, the one or more passive attenuation models being determined according to the captured ambient sound.
  • the one or more passive attenuation models may be an adaptive digital filter.
  • the processor may be further configured to perform a subtraction of the estimate of the residual ambient SPL from the canal SPL.
  • An estimation of wearer-induced disturbances (WID) SPL present in the ear canal may be determined according to the subtraction.
  • a calibration of the one or more passive attenuation models may be performed according to the subtraction.
  • the processor may be adapted to execute an adaptive algorithm to calibrate the one or more passive attenuation models according to the subtraction.
  • a system to measure noise reduction and evaluate contributions of a playback sound pressure level (SPL) of a sound dose present in an ear canal of a hearing protection device (HPD) wearer comprising an inner ear microphone (IEM) adapted to capture a canal sound pressure level (SPL) of the sound dose present in the ear canal, an in-ear loudspeaker (IELS) configured to emit a playback signal in the ear canal, according to at least one sound source.
  • the system further comprising a processor in signal communication with the IEM and the IELS, the processor being configured to estimate a playback SPL according to the canal SPL.
  • the estimate of the playback SPL may be computed according to at least one IELS-IEM model, the at least one IELS-IEM model being determined according to the at least one sound source.
  • the at least one IELS-IEM model may be an adaptive digital filter.
  • the playback signal may be emitted according to a plurality of sound sources and wherein the processor is further configured to estimate the playback SPL for each of the plurality of sound sources.
  • the processor may be further configured to perform a subtraction of the estimated playback SPL from the canal SPL.
  • An estimation of wearer- induced disturbances (WID) SPL present in the ear canal may be determined according to the subtraction.
  • WID wearer- induced disturbances
  • a calibration of the at least one IELS-IEM model may be performed according to the subtraction.
  • An adaptive algorithm may be determined for the calibration, the adaptive algorithm being determined according to the subtraction.
  • FIG. 1 is an illustration of a system to measure noise reduction and evaluate the contributions of various sound sources to noise exposure dose of exposition using electro- acoustic earplugs.
  • FIG. 2 a calibration phase/modeling phase of a passive attenuation model according to the principles of the present invention.
  • FIG. 3 a calibration phase/modeling phase of an IELS-IEM model according to the principles of the present invention.
  • FIG. 4 is an example graph of an amplitude of a response of a passive attenuation model as a function of the frequency according to the principles of the present invention.
  • FIG. 5 is example graph of the amplitude of the response of an IELS-IEM model as a function of the frequency according to the principles of the present invention.
  • FIG. 6 is an example graph of the amplitude of the correction of a passive attenuation model and of an IELS-IEM model as a function of the frequency according to the principles of the present invention.
  • the system 100 may be implemented as an advanced HPD in the form of an electro-acoustical earplug.
  • the earplug 1 comprises an OEM 10 and an IEM 12.
  • the earplug 1 may further comprise an IELS 14, generally adapted for playback of audio 4 and communication signals 5.
  • the IELS 14 may be controlled to lower or increase the volume of sound emitted by the OEM 10, the audio 4 and communication signals 5.
  • the earplug 1 may further comprise a processing device, such as a processor or a controller, and a memory unit allowing to store instructions to be executed or any data needed to execute the said instructions.
  • the audio 4 and communication 5 signals provide separated contributions to a noise dose received in the ear canal 50.
  • the earplug 1 is configured to calculate estimates of the various electro-acoustical paths from sound sources to the inner end of the earplug using different models, such as models using adaptive filters.
  • the HPD 1 is inserted into the ear canal 50 of a user.
  • the HPD 1 may be configured to have audio playback 4 and/or communication 5 capabilities.
  • a user When worn by the user, a user’s sound exposure or sound dose typically comprises three major classes of exposure sources: the residual ambient noise or sounds 52, sounds 4, 5 emitted by the IELS 14 and/or wearer-induced disturbances (WID) 56.
  • the residual ambient noise or sounds 52 sounds 4, 5 emitted by the IELS 14 and/or wearer-induced disturbances (WID) 56.
  • WID wearer-induced disturbances
  • the ambient noise or sound 2 surrounding the ear of the user is attenuated by the HPD 1.
  • the HPD 1 acts as a passive attenuation 40 resulting in in residual ambient noise or sound 52 present in the ear canal 50.
  • the IELS 14 produces an audio playback 4, a communication signal 5 or any other audio signal.
  • the IELS 14 is typically connected to the OEM 10 which captures the ambient sounds 2.
  • a level dependent attenuation module 75 is configured to varies the level of the ambient sounds 2 captured by the OEM 10.
  • the level dependent attenuated signal 6, the audio signals 4 and/or the communication signals 5 may receive additional processing 77 to manipulate the inputted sounds sources through mathematic formulae or algorithms to output respective resulting signals 7.
  • the sounds from the different sources such as the audio playback 4, a communication signal 5 and/or the level dependent attenuated signal 6, may be merged, combined or mixed prior to be emitted by the IELS 14.
  • the signals 4, 5 and/or 6 are mix using any mixing device 78.
  • the resulting mix audio signal 8 is inputted in the IELS which is configured to emit the said signal 8 in the ear canal.
  • the audio signal 8 contributes to the sound exposure or dose of the ear canal 50 in the form of playback sound 54.
  • wearer-induced disturbances (WID) 56 such as talking, chewing or any other wearer inner sounds, contribute to the sound exposure in the form of bone- conducted acoustical signals 56 that are amplified by the occlusion effect present in the ear canal 50.
  • the IEM 12 of the HPD 1 is generally positioned in the ear canal 50 to capture the sound exposure or dose within the said ear canal 50.
  • the output of the IEM 12 is the IEM sound pressure level (SPL) 58.
  • the HPD calculates an estimated playback SPL 72 in the ear canal 50 and calculates an estimated residual ambient SPL 62.
  • the HPD uses an IELS-IEM model 70 to calculate the estimated playback SPL 72 and a passive attenuation model 60 to calculate the estimated residual ambient SPL 62.
  • the estimated playback SPL 72 and the estimated residual ambient SPL 62 are subtracted from the IEM SPL 58.
  • the subtraction process 46 is typically executed using the processor or controller of the HPD 1.
  • the resulting signal of the subtraction process 46 is an estimated WID SPL 80.
  • the resulting estimated SPL 62, 72 and 80 represents an estimation of the different components of the sound dose within the ear canal 50.
  • the estimated ambient SPL 62 of the contribution of ambient noise 52 is calculated using a passive attenuation model 60.
  • the passive attenuation models use the SPL captured by the OEM as input.
  • the passive attenuation model 60 typically calculates a transfer function estimate of the noise reduction or attenuation of the HPD 1 using an adaptive digital filter.
  • Such adaptive digital filter models the acoustical path between the OEM 10 and the IEM 12. Understandably, any known method to evaluate or to compute the attenuation of the HPD 1 may used within the scope of the present invention.
  • the passive attenuation model 60 may be calibrated to offer a better estimate of the passive attenuation 40 of the HPD 1.
  • the adaptive filter is calibrated during an identification or calibration phase.
  • the identification phase comprises having ambient sounds being present in the ear canal 50.
  • only residual ambient sounds 52 will be present in the ear canal 50 to obtain better calibration results.
  • the residual ambient sounds 52 will be compared to the sounds captured by the OEM 10 to calibrate the passive attenuation model 60. Understandably, other known calibration methods to calculate the attenuation of the HPD may be used within the scope of the present invention.
  • This identification or calibration phase may be triggered manually, such as by the user or may be executed periodically at pre-determined time intervals, or executed upon predetermined conditions being detected. Suitable conditions may comprise, but are not limited to, high sound pressure levels being detected by the OEM 10 and low sound pressure levels being detected by the IEM 12.
  • the filter shall converge to a noise reduction model or value associated with the HPD 1.
  • the calibrated filter is then executed to filter the OEM 10 signal which is dominated by ambient sound.
  • the calibrated filter outputs an estimate 62 of the portion of sound energy present inside the ear canal 50 due to residual ambient noise 52 using the calculated noise reduction model or value.
  • the calibration phase/modeling phase 200 of the passive attenuation model 60 is illustrated.
  • an adaptive algorithm 66 uses the resulting signal e(n) 65 as input to update or recalculate the passive attenuation model 60.
  • a known ambient SPL 2 captured by the OEM 10 x(n) is fed to the passive attenuation model 60.
  • the estimated residual ambient SPL 62 is calculated and is subtracted 46 from the sound dose captured by the OIM 12.
  • the resulting signal e(n) 65 is used by the adaptive algorithm to calibrate or update the model 60.
  • the estimation of the contribution of playback sound 72 to sound exposure relies on a model of the transfer function of the electro-acoustical path from the input of the IELS 14 to the output of the IEM 12 using an IELS-IEM model 70, such as an adaptive digital filter.
  • the IELS-IEM model 70 uses the digitally processed output signals 7 or the audio signals 4, the communications signal 5 and the level dependent attenuated signal 6 as different inputs.
  • the IELS-IEM model 70 calculates an estimate of each of the signals 4, 5, 6 to produce different playback SPL 72. Understandably, the present estimation may be configured to use a mixdown signal 8 of the audio signals 4, 5, 6 to output a single playback SPL 72
  • the filter within the model 70 may be calibrated during an identification or calibration phase.
  • identification phase generally comprises the step of the IELS 14 producing a test signal 9 in the ear canal 50.
  • the identification phase may be manually triggered, such as- triggered by the user, may be automatically executed at pre-defmed time intervals, or may be automatically executed when suitable conditions are detected.
  • the suitable conditions may comprise, but are not limited to, any signals being currently played back through the IELS 14, while low sound pressure levels are detected by the OEM 10.
  • the estimation model or value may be provided to the filter of the model 70.
  • the estimation model or value may be readily available from a communication earpiece adapted to provide echo cancellation.
  • Echo cancellation is generally used to prevent echo in full-duplex communication systems. Echo cancellation generally relies on modeling the path between the input of the IELS 14 to the output of the OEM 10.
  • the identification phase further comprises accurately calculating the estimation models by letting the filter of the model 70 converging to the estimation models and/or values of the electro-acoustical path between the IELS 14 and the IEM 12.
  • the calibration phase/modeling phase 300 of the IELS- IEM model 70 is illustrated.
  • the system 100 further comprises an emitting device 77 for producing a test signal 9.
  • the test signal 9 is emitted by the loudspeaker 14 in the ear canal and in the IELS-IEM model 70 at time of calibration.
  • the IELS-IEM model 70 computes an estimate of the test signal 72 which is subtracted from the sound dose captured by the IEM 12.
  • the resulting signal 75 (e(n)) is processed using an adaptive algorithm or instructions 76 to update or recalculate the IELS-IEM model 70.
  • the resulting signal 75 from the subtraction 46 may be corrected and used in a diagnostic module 49 or may be used during a calibration period.
  • the calibrated filter is used to filter incoming audio signals, either separately
  • the estimation of the contribution of WIDs 56 is obtained by elimination or subtraction 46. From the IEM 12 signal, which measures all or most of the sounds present in the ear canal 50, the predefined portions of sound energy attributable to ambient residual noise 52 and playback sounds 54 may be removed, leaving the portion of sound energy present in the ear canal due to WIDs 56.
  • the HPD or electro-acoustical earpiece 1 may comprise an ear tip having a sound channel (not shown) to which is coupled the IEM 12.
  • the IEM 12 is not directly located inside the ear canal 50, but rather acoustically coupled to the ear canal 50 through the sound channel.
  • the ear tip or sound channel is adapted be sealingly fitted to the walls of the ear canal 50. Such seal generally aims at providing a hearing protection.
  • the IEM 12 signal is not identical to that present inside the ear canal 50, at the inner end of the ear tip.
  • the HPD or electro-acoustical earpiece 1 may be configured to calculate a correction of the estimates SPL outputted by the filters 62, 72 and/or of the estimated WID SPL 80.
  • the correction may differ depending on whether the source of sound exposure is ambient noise 52, playback sound 54 and/or WIDs 56.
  • a separate correction can therefore be used for each of these source classes, such as WID contribution correction 22, IEM playback correction 24 and/or IEM ambient correction 26.
  • Such corrections 22, 24 and 26 are applied to the estimated SPL 62, 72 and 80 to obtain respective corrected signals 64, 74 and 84.
  • these corrections 22, 24 and/or 26 can be pre-calculated using acoustical models, or pre-measured using calibration procedures, and applied separately to each estimated contributive signal to obtain a corrected estimation of the sound pressure level at the inner-end of the ear tip.
  • the transfer function is independent of the source and a single correction may be used.
  • the method comprises temporarily applying one or more weightings in the dose calculation 47 to the contribution of all sources when WIDs 56 are present in significant amount.
  • a personal attenuation rating (PAR) 34 may be estimated using the ambient SPL 2 provided by the OEM 10 and the estimate of the residual ambient SPL 62.
  • the HPD may be configured to calculate a first A- weighting value 32 of the ambient SPL 2.
  • the HPD 1 is further configured to calculate a second A-weighting value 30 of the estimated residual ambient SPL 62.
  • the HPD 1 is further configured to subtract the second A-weighting 30 from the first A-weighting 32 to obtain the PAR estimate 34.
  • the PAR estimate 34 generally providers another parameter in the analysis of the estimated components 62, 72 and 80 of the sound dose in the ear canal 50.
  • the PAR estimate value 34 generally provides a continuous estimation of the IEM signal that is free of disturbances such as WID 56 or playback sounds 54 that can be used to estimate the PAR, and can capture variations in the PAR 34 that are due to variations in the spectral content of the ambient noise.
  • the estimated SPL 62, 72, 80 and/or corrected estimated SPL 64, 74, 84 may be inputted to a diagnostic module 49.
  • the diagnostic module 49 may be configured to calculate suggestion or recommended actions for the user based on the different values of the inputted estimated SPL 62, 72, 80 and/or corrected estimated SPL 64, 74, 84.
  • the diagnostic module 49 may suggest to a user to move to a calmer area as the total sound dose of the ear canal 50 exceeds a predetermined level and the weight of the estimated residual ambient SPL 62 exceed the weights of the other estimated components 72 or 80 or exceeds a predetermined level.
  • the diagnostic module 49 may suggest to the user to reduce the sound of the audio signal 4 or to suggest reducing the number of calls producing the communication signal 5.
  • the sound levels of the communication signals 5 or audio signals 4 may be automatically reduces when an overall SPL exceeds a predetermined value and the weights of such signal 4, 5 also exceed one or more predetermined levels.
  • the system 100 may further comprise a module to calculate the dose in the ear canal 47 using as input the separated estimated sound dose components 62, 72, 80 and/or the corrected values 64, 74 or 84.
  • the resulting values may be SPL of each of the components or combined values of each component.
  • the diagnostic module 49 may be fed by standard or best practices in dosimetry.
  • a comparison module 48 uses as input the separated and/or combined dose calculation 47 and compares the said dose calculation with the standard and best practices.
  • the resulting value may be inference values or boolean values indicating if the said separated or combined doses are within the boundaries of the standard and/or best practices values.
  • the system 100 may further comprise a graphical user interface (GUI) 90 adapted to communicate, display and/or read the suggestions or recommendations calculated by the diagnostic module 49. Understandably, any GUI 90 may be used such as displaying results on a mobile device or a computer, communicating the results through a network or using the loudspeaker 14 to read the suggestion to the wearer.
  • GUI graphical user interface
  • the system 100 comprises an OEM 10 and an IEM 12 within the ear canal 50.
  • the system 100 comprises an earplug or attenuation device 1 having a form of passive attenuation 40, such as a plug.
  • the system 100 further comprises a DSP or processing device 44, such as a processor or a controller, and may comprise a memory unit allowing to store instructions to be executed or any data needed to execute the said instructions.
  • the processing device 44 is configured to calculate and/or compute an estimate value 62 of the residual ambient SPL 52 present in the ear canal 50 based on the ambient SPL 2 captured by the OEM 10.
  • the estimation is typically computed using a passive attenuation model 60, such as an adaptive digital filter.
  • the system 100 further comprises a subtraction module 46 adapted to subtract the estimated ambient SPL 62 from the sound dose captured by the IEM 12 within the ear canal 50. As explained above, the resulting signal containing the estimated WID SPL 80 from the subtraction 46 may be corrected and used in a diagnostic module 49.
  • the system 100 comprises an IEM 12 within the ear canal 50 and an IELS 14, generally adapted for playback of audio 4 and communication signals 5, as shown in FIG. 1.
  • the system 100 comprises an earplug or attenuation device, such as a plug.
  • the system 100 further comprises a DSP or processing device 44, such as a processor or a controller, and may comprise a memory unit allowing to store instructions to be executed or any data needed to execute the said instructions.
  • the signals provide separated contributions to a noise dose received in the ear canal 50.
  • the processing device 44 is configured to calculate and/or compute an estimate value 72 of the playback SPL 54 present in the ear canal 50 based on the playback source signal, such as audio 4 and communication 5 signals.
  • the estimation is typically computed using an IELS-IEM model 70 for the combined signal 8 (see FIG. 1) or for each component, such as the audio signal 4 or the communication signal 5.
  • FIG. 4 an example graph of the amplitude of the response of the passive attenuation model as a function of the frequency 400 is illustrated. The response for the left 402 and right 404 ears are illustrated. [0079] Referring now to FIG. 5, an example graph of the amplitude of the response of the
  • IELS-IEM model as a function of the frequency 500 is illustrated.
  • the responses for the left 502 and right 504 ears are illustrated.
  • FIG. 6 an example graph of the amplitude of the correction of the passive attenuation model 602 and of the IELS-IEM model 604 as a function of the frequency 600 is illustrated.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Physics & Mathematics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Otolaryngology (AREA)
  • General Health & Medical Sciences (AREA)
  • Psychology (AREA)
  • Biophysics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Animal Behavior & Ethology (AREA)
  • Signal Processing (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Multimedia (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)

Abstract

L'invention concerne un système et un procédé permettant de mesurer une réduction de bruit et d'évaluer les contributions de diverses sources sonores à une dose d'exposition au bruit d'une exposition utilisant des bouchons d'oreille électro-acoustiques. Le système peut être mis en œuvre sous la forme d'un HPD avancé sous la forme d'un bouchon d'oreille électro-acoustique. Le bouchon d'oreille comprend un OEM 10 et un IEM. Le système est conçu pour calculer un signal IEM estimé sur la base du calcul d'estimations de bruit ambiant résiduel, de sons de reproduction ou de WID présents dans le conduit auditif.
PCT/CA2020/051481 2019-11-01 2020-11-01 Système et procédé pour effectuer une dosimétrie de bruit intra-auriculaire et une évaluation d'affaiblissement personnelle sous un bouchon d'oreille électro-acoustique tout en excluant les perturbations induites par le porteur et en séparant les sources d'exposition WO2021081671A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP20881596.9A EP4052028A4 (fr) 2019-11-01 2020-11-01 Système et procédé pour effectuer une dosimétrie de bruit intra-auriculaire et une évaluation d'affaiblissement personnelle sous un bouchon d'oreille électro-acoustique tout en excluant les perturbations induites par le porteur et en séparant les sources d'exposition
US17/758,988 US20230035275A1 (en) 2019-11-01 2020-11-01 System and method to perform in-ear noise dosimetry and personal attenuation rating under an electro-acoustic earplug while excluding wearer-induced disturbances and separating exposure sources

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201962929368P 2019-11-01 2019-11-01
US62/929,368 2019-11-01

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WO2021081671A1 true WO2021081671A1 (fr) 2021-05-06

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008061260A2 (fr) 2006-11-18 2008-05-22 Personics Holdings Inc. Procédé et dispositif d'écoute personnalisée
WO2008138349A2 (fr) 2007-05-10 2008-11-20 Microsound A/S Procédé et système pour une meilleure gestion des sons fournis par des écouteurs
US20130094658A1 (en) * 2011-10-17 2013-04-18 Honeywell International Inc. Sound exposure monitor for hearing protection device
US9167365B2 (en) * 2003-12-05 2015-10-20 3M Innovative Properties Company Method and apparatus for objective assessment of in-ear device acoustical performance
US20190075412A1 (en) * 2006-06-14 2019-03-07 Staton Techiya, Llc Earguard Monitoring System

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9167365B2 (en) * 2003-12-05 2015-10-20 3M Innovative Properties Company Method and apparatus for objective assessment of in-ear device acoustical performance
US20190075412A1 (en) * 2006-06-14 2019-03-07 Staton Techiya, Llc Earguard Monitoring System
WO2008061260A2 (fr) 2006-11-18 2008-05-22 Personics Holdings Inc. Procédé et dispositif d'écoute personnalisée
WO2008138349A2 (fr) 2007-05-10 2008-11-20 Microsound A/S Procédé et système pour une meilleure gestion des sons fournis par des écouteurs
US20130094658A1 (en) * 2011-10-17 2013-04-18 Honeywell International Inc. Sound exposure monitor for hearing protection device

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP4052028A4

Also Published As

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EP4052028A4 (fr) 2023-12-13
EP4052028A1 (fr) 2022-09-07
US20230035275A1 (en) 2023-02-02

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